EP1471765A2 - Adaptive Rückkopplungsunterdrückung - Google Patents

Adaptive Rückkopplungsunterdrückung Download PDF

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Publication number
EP1471765A2
EP1471765A2 EP04251656A EP04251656A EP1471765A2 EP 1471765 A2 EP1471765 A2 EP 1471765A2 EP 04251656 A EP04251656 A EP 04251656A EP 04251656 A EP04251656 A EP 04251656A EP 1471765 A2 EP1471765 A2 EP 1471765A2
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EP
European Patent Office
Prior art keywords
feedback
adaptive
bandpass
input signals
input
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EP04251656A
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English (en)
French (fr)
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EP1471765A3 (de
Inventor
Henry Luo
Horst Arndt
André Vonlanthen
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Unitron Hearing Ltd
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Unitron Hearing Ltd
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R3/00—Circuits for transducers, loudspeakers or microphones
    • H04R3/02—Circuits for transducers, loudspeakers or microphones for preventing acoustic reaction, i.e. acoustic oscillatory feedback
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically

Definitions

  • the invention relates to audio systems and a method for adaptively canceling feedback. More particularly, the invention relates to a hearing aid system and method for adaptively canceling feedback while not impairing the speech comprehension of the user of the hearing aid system.
  • Feedback in hearing aid systems is a well-known problem that can occur when there is a feedback path from the output signal of the hearing aid system to the input signal of the hearing aid system. This usually occurs when a user of the hearing aid system is moving his/her jaws (i.e. while eating), wearing a hat, using a telephone, standing close to walls, etc.
  • the feedback usually occurs in mid and high frequency regions which are important for allowing the hearing aid user to understand speech. Accordingly, feedback is not only annoying but impairs speech comprehension for the hearing aid user. Feedback can also be due to other causes such as magnetic, vibrational or electrical.
  • Some of these approaches comprise estimating a feedback path transfer function and altering the feedback path transfer function at critical frequencies (i.e. feedback prone frequencies) to remove feedback.
  • the feedback path transfer function can be estimated via auto-correlation of the input signal and/or cross-correlation of the input signal and the output signal.
  • This approach may also be adaptive by incorporating a variation of the Least Mean Square algorithm for adaptive estimation of the feedback transfer function. Consequently, this approach requires rather high levels of computational power, and due to the limited computational power of available digital hearing aid systems, the effectiveness of this approach is restricted particularly in dealing with the multiple feedback paths that usually occur in daily life.
  • a single notch filter may effectively reduce feedback when the overall loop gain in a single narrow frequency band reaches values larger than unity and the phase of the feedback signal is 0° or a multiple of 360° (i.e. the Nyquist criterion). If the loop gain begins to exceed unity and the corresponding phase satisfies the Nyquist criterion in several frequency bands that lie far apart, then several notch filters may be used. However, the notch filters have to be tuned to the correct frequencies at which the feedback occurs which implies that the frequencies and frequency bands where feedback occurs must be detected.
  • Detection of a single frequency feedback signal in noise may involve signal processing techniques such as correlation and parametric modeling methods, followed by peak picking, zero crossing counters, etc., as is well known to those skilled in the art. Accordingly, this method of feedback cancellation also requires high levels of computational power that can exceed the computational power available in hearing aid systems.
  • anti-phase feedback canceling Another approach for reducing feedback in the hearing aid system is anti-phase feedback canceling. This involves adaptively detecting changes in the feedback path, and once feedback is detected, generating an anti-phase feedback signal to cancel the feedback. If the hearing aid system is linear, the feedback path changes slowly, and only a small number of feedback paths exist (such as one or two), anti-phase feedback canceling works well. However, the feedback path can change dramatically and very rapidly in real-life situations. Furthermore, most of the advanced digital hearing aid systems are not linear and incorporate some type of input or output referred compression. Accordingly, the gain of the hearing aid system changes constantly as the input or output signal levels change. The feedback signal level is therefore not constant, as it is for a linear hearing aid system. In addition, multiple feedback paths usually occur as well as temporary feedback path changes. All of these factors result in high computational demand which can limit the application of the anti-phase feedback canceling technique in hearing aid systems, particularly when dealing with multi-feedback path situations.
  • the most basic feedback manager is a static feedback manager that permanently reduces the maximum loop gain to prevent the occurrence of feedback in the hearing aid system.
  • This approach can be effective, reducing the maximum system gain limits the user's access to higher gain, which may be required on occasion depending on the individuals hearing loss. Since feedback often occurs in the higher frequency range, which is also the frequency range that contains the consonant sounds of speech, reducing the gain in this frequency range can have detrimental effects on speech discrimination.
  • the static feedback manager cannot dynamically compensate for temporary feedback caused when a hand or a telephone is placed close to or on the hearing aid system, or if the user distorts the ear canal with jaw movements.
  • the present invention is directed towards a hearing aid system that reliably and rapidly detects feedback or the onset of feedback and rapidly eliminates the feedback once it is detected while requiring minimal computational cost. Accordingly, a wearer of the hearing aid system is not subjected to any annoying or upsetting feedback signals during a telephone call, or during meals and other daily activities requiring jaw movements.
  • the feedback detection and elimination is adaptive in time, frequency and amplitude. Further, the elimination of feedback is done while maintaining good sound quality of the output sound signal to the user of the hearing aid system.
  • the invention provides an audio system for receiving a time domain input signal having an input frequency spectrum and for providing a time domain output signal.
  • the invention can remove feedback from the system or prevent feedback from occurring in the system.
  • the audio system comprises an analysis unit for receiving the time domain input signal and for providing N bandpass input signals, each of the bandpass input signals corresponding to a portion of the input frequency spectrum, and wherein N is a positive integer.
  • the audio system also comprises an adaptive feedback cancellation unit coupled to the analysis unit for receiving the N bandpass input signals and providing N bandpass output signals.
  • the adaptive feedback cancellation unit comprises N sub-units. At least one of the sub-units is adapted to cancel feedback.
  • the at least one sub-unit includes: (i) a feedback detector coupled to the analysis unit for receiving one of the bandpass input signals and providing a feedback detection signal for indicating the presence of a feedback condition in one of the bandpass input signals, (ii) an adaptive feedback canceller coupled to the feedback detector for receiving the feedback detection signal and providing an adaptive gain modification factor for adjusting gain when the feedback detection signal indicates the presence of the feedback condition within the bandpass input signals, and, (iii) a multiplier coupled to the adaptive feedback canceller and the analysis unit for providing one of the bandpass output signals based on one of the bandpass input signals and the adaptive gain modification factor.
  • the audio system further comprises a synthesis unit for receiving the N bandpass output signals and for providing the time domain output signal.
  • the invention provides a method for removing a feedback condition in a audio system.
  • the audio system receives a time domain input signal having an input frequency spectrum and provides a time domain output signal.
  • the method comprises:
  • the invention provides an audio system for receiving a time domain input signal having an input frequency spectrum and for providing a time domain output signal.
  • the audio system is adapted to remove a feedback condition within the time domain input signal.
  • the audio system comprises an analysis unit for receiving the time domain input signal and providing N bandpass input signals. Each of the bandpass input signals correspond to a portion of the input frequency spectrum, and wherein N is a positive integer.
  • the system further comprises an adaptive feedback cancellation unit coupled to the analysis unit for receiving the N bandpass input signals and providing N bandpass output signals.
  • the adaptive feedback cancellation unit comprises N sub-units, wherein at least one sub-unit comprises means for canceling feedback by detecting the presence of the feedback condition in at least one of the bandpass input signals and providing at least one adaptive gain modification factor for adjusting gain for the at least one of said bandpass input signals to remove the feedback condition and provide at least one of the bandpass output signals.
  • the system also includes a synthesis unit for receiving the N bandpass output signals and for providing the time domain output signal.
  • the present invention provides a method for removing a feedback condition in an audio system.
  • the audio system is adapted to receive a time domain input signal having an input frequency spectrum and provide a time domain output signal.
  • the method comprises:
  • Figure 1 is a block diagram of a first embodiment of a hearing aid system for adaptively detecting and canceling feedback in accordance with the present invention
  • Figure 2 illustrates a typical change in sound level that occurs during a feedback condition for a linear hearing aid system
  • Figure 3 illustrates a typical change in sound level that occurs during a feedback condition for a non-linear hearing aid system
  • Figure 4 is a magnified view of the change in sound level of Figure 3;
  • Figure 5 is an exemplary plot of a gain curve for the hearing aid system of Figure 1;
  • Figure 6 is an exemplary plot of an actual gain curve for the hearing aid system of Figure 1 when a fixed feedback margin is applied by the hearing aid system;
  • Figure 7 is an exemplary plot of an actual gain curve for the hearing aid system of Figure 1 when an adaptive feedback margin is applied by the hearing aid system;
  • Figure 8 is a block diagram of an alternative embodiment of a hearing aid system for adaptively reducing feedback while incorporating a volume control unit before an adaptive feedback cancellation unit in accordance with the present invention
  • Figure 9 is an exemplary plot of an actual gain curve for the hearing aid system of Figure 8 when a fixed feedback margin is applied by the hearing aid system;
  • Figure 10 is an exemplary plot of an actual gain curve for the hearing aid system of Figure 8 when an adaptive feedback margin is applied by the hearing aid system;
  • FIG 11 is a block diagram of another alternative embodiment of a hearing aid system for adaptively reducing feedback while incorporating a volume control unit after an adaptive feedback cancellation unit in accordance with the present invention
  • Figure 12 is an exemplary plot of an actual gain curve for the hearing aid system of Figure 11 when a fixed feedback margin is applied by the hearing aid system;
  • Figure 13 is an exemplary plot of an actual gain curve for the hearing aid system of Figure 11 when an adaptive feedback margin is applied by the hearing aid system.
  • FIG. 1 illustrates a hearing aid system 10 that is a particular example of an audio system in accordance with a first preferred embodiment of the present invention.
  • the hearing aid system 10 comprises a microphone 12 , an analog- to-digital converter (ADC) 14 , an analysis unit 16 , an adaptive feedback cancellation unit 18 , a synthesis unit 20 , a digital-to-analog converter (DAC) 22 and a receiver 24 .
  • ADC analog- to-digital converter
  • DAC digital-to-analog converter
  • Receive 24 can include other input means such as multiple microphones, an induction pick-up coil, a direct electrical input or a bone conduction input as is well known to those skilled in the art. For simplicity, this description focuses on a microphone input.
  • the microphone 12 receives an input sound signal 26 and provides an analog input signal 28 corresponding to input sound signal 26 .
  • the input sound signal 26 contains desirable audio information, noise and possibly feedback.
  • the microphone 12 may be any type of sound transducer capable of receiving a sound signal and providing a corresponding analog electrical signal.
  • the ADC 14 receives the analog input signal 28 and produces a time domain input signal 30 which is digital.
  • the time domain input signal 30 has an input frequency spectrum. Further processing is preferably performed on the time domain input signal 30 such as framing and filtering with a low-pass filter.
  • the time domain input signal 30 may then preferably be folded and added to generate a block of data for processing by the analysis unit 16 . These operations are well known to those skilled in the art and are not shown in Figure 1.
  • the analysis unit 16 receives the time domain input signal 30 and produces one or more bandpass input signals 32-1, 32-2, ..., 32-N which each corresponds to a portion of the input frequency spectrum of the time domain input signal 30 .
  • the value of N may be any integer but is preferably a power of 2 such as 2, 4, 8, 16, etc.
  • the analysis unit 16 may perform a time domain to frequency domain transform, such as the Fast Fourier Transform (FFT) or the Wavelet Transform, or may comprise a filter bank of FIR or IIR filters for providing the bandpass input signals 32-1, 32-2, ..., 32-N .
  • the analysis unit 16 preferably performs a 2N-point FFT to generate the bandpass input signals 32-1, 32-2, ..., 32-N .
  • the coefficients of the 2N-point FFT represent N frequency bands.
  • the signal strength (i.e. input sound level) of the bandpass input signals 32-1, 32-2, ..., 32-N can be determined from the corresponding FFT coefficient.
  • the input sound level will vary with time and frequency.
  • any one of the bandpass input signals 32-1, 32-2, ..., 32-N may contain feedback. Accordingly, each of the bandpass input signals 32-1, 32-2, ..., 32-N is processed by the adaptive feedback cancellation unit 18 which provides a corresponding set of bandpass output signals 34-1, 34-2, ..., 34-N which do not have feedback.
  • the synthesis unit 20 combines the bandpass output signals 34-1, 34-2, ..., 34-N into a time domain output signal 36 which is a digital signal. Accordingly, the synthesis unit 20 may perform the Inverse Fast Fourier Transform (IFFT), the inverse Wavelet transform or may comprise a summer depending on the processing that is performed by the analysis unit 16 .
  • IFFT Inverse Fast Fourier Transform
  • the time domain output signal 36 is then converted to an output analog signal 38 which is processed by the receiver 24 for providing an output sound signal 40 to the user of the hearing aid system 10.
  • the receiver 24 may be a zero-bias receiver and the time domain output signal 36 may be directly applied to the receiver 24 without passing through the DAC 22 .
  • the hearing aid system 10 further comprises other components for processing the bandpass input signals 32-1, 32-2, ..., 32-N, as is commonly known to those skilled in the art, such as an amplification unit (not shown) and/or a noise reduction unit.
  • the amplification unit applies a gain value to each of the bandpass input signals 32-1, 32-2, ..., 32-N for amplifying these signals according to the hearing loss of the user of the hearing aid system 10 thereby allowing the user to hear speech.
  • the amplification unit may utilize a linear gain curve, in accordance with typical linear hearing aid systems, as is commonly known to those skilled in the art, to calculate the gain values depending on the sound level of the bandpass input signals 32-1, 32-2, ..., 32-N.
  • the amplification unit may utilize a non-linear gain curve, in accordance with typical compression hearing aid systems, as is commonly known to those skilled in the art, to calculate the gain values depending on the sound level of the bandpass input signals 32-1, 32-2, ..., 32-N. This is discussed in further detail below.
  • the adaptive feedback cancellation unit 18 comprises a number of sub-units 18-1, 18-2, ..., 18-N for processing each of the bandpass input signals 32-1, 32-2 , .., 32-N .
  • Each sub-unit of the adaptive feedback cancellation unit 18 comprises a feedback detector 42 , an adaptive feedback canceller 44 and a multiplier 46 .
  • the bandpass input signal 32-1 is split into two parts; one part of the bandpass input signal 32-1 is received by the feedback detector 42-1 and the other part of the bandpass input signal 32-1 is received by the multiplier 46-1 .
  • the feedback detector 42-1 processes the bandpass input signal 32-1 to determine the presence of a feedback condition in the frequency range associated with the bandpass input signal 32-1.
  • the feedback condition includes two scenarios: feedback already exists in the bandpass input signal 32-1 or there is the onset of feedback (i.e. the buildup of feedback) in the bandpass input signal 32-1 .
  • the feedback detector 42-1 provides a feedback detection signal FD-1 for indicating the presence of the feedback condition in the bandpass input signal 32-1 .
  • the feedback detection signal FD-1 may be a binary signal, for example, with a value of 1 for indicating the presence of the feedback condition and a value of 0 for indicating that the feedback condition is not present.
  • the adaptive feedback canceller 44-1 receives the feedback detection signal FD-1 and computes an adaptive gain modification factor G-1 with an appropriate magnitude when the feedback condition has been detected.
  • the adaptive gain modification factor G-1 adjusts the amount of gain that is applied to the bandpass input signal 32-1 by the amplification unit for removing feedback or preventing the further buildup of feedback within the bandpass input signal 32-1 . If the feedback condition is not detected within the bandpass input signal 32-1 then the adaptive feedback canceller 44-1 may provide an adaptive gain modification factor G-1 with a magnitude of 1.
  • the multiplier 46-1 multiplies the bandpass input signal 32-1 with the adaptive gain modification factor G-1 to produce the bandpass output signal 34-1.
  • the feedback detectors 42-1, 42-2, ..., 42-N continuously monitor the bandpass input signals 32-1, 32-2, ..., 32-N to detect the feedback condition in real time independently and simultaneously in all N frequency bands.
  • the feedback detectors 42-1, 42-2 ..., 42-N also utilize a sliding time window to analyze the corresponding bandpass input signal 32-1, 32-2, ..., 32-N.
  • the size of the sliding time window and the rate at which the sliding time window is updated can be selected to allow for the rapid detection of the feedback condition in the bandpass input signals 32-1, 32-2, ..., 32-N .
  • the simultaneous and independent monitoring of a plurality of frequency bands allows for the detection of multiple, simultaneous feedback paths.
  • most modern hearing aid systems employ FFT or filter-bank processing (i.e.
  • the adaptive feedback cancellation scheme of the present invention does not add an excessive amount of computational complexity to a hearing aid system but rather efficiently utilizes resources that are already present in the hearing aid system.
  • FIG. 3 shown therein is the development of feedback for a non-linear (i.e. compressive) hearing aid system for a bandpass input signal.
  • the input sound level increases gradually due to feedback build-up from time t 0 to time t 1 during which the input sound level crosses the sound level threshold l 0 and output limitation occurs for the sound levels of the output and input controlled compression system.
  • the output sound level will not be saturated at a constant sound level l s but rather will be modulated between upper and lower bounds represented by the dotted lines in Figure 3.
  • the feedback will be modulated since, the compression unit of the non-linear hearing aid, will provide a gain reduction for an input sound signal with a high sound level.
  • the sound level of the output sound signal will be reduced, which leads to a reduction in the sound level of the input sound signal that is leaked back to the microphone from the receiver.
  • the compression unit will then apply a larger gain to the input sound signal that leads to a larger amount of feedback. This process repeats itself until the feedback loop is broken or feedback is removed from the input sound signal.
  • the degree of modulation in the feedback depends on the feedback path and the dynamic characteristics of the particular compression method that is used by the non-linear hearing aid system. These dynamic characteristics include attack and release times, the particular compression ratios that are used by the compression unit and the interactive relationship between these parameters. Typical level variations for a modulated feedback signal are system dependent and may range from 6 to 10 dB, while the feedback modulation frequency could vary from a few Hz to a few hundred Hz.
  • the input sound level is preferably represented by the magnitude of the corresponding FFT coefficient provided by the analysis unit 16.
  • the detection parameters that may be used to detect the onset of feedback or the presence of feedback include input sound level, input sound level variation, input sound level modulation, rise time duration, and gain differential. These detection parameters will be described in relation to bandpass input signal 32-1 and feedback detector 42-1 .
  • average values for these detection parameters are measured on data blocks of the bandpass input signals.
  • the data blocks have a pre-specified time duration and a sliding window is used in constructing the data blocks.
  • the time duration of each data block can be adjusted to allow the hearing aid system to more quickly attack feedback (by reducing the time duration of each data block) or more slowly attack feedback (by increasing the time duration of each data block).
  • the inventors provide numerical examples for the parameters that are used to detect the onset or presence of feedback in a hearing aid system. These numerical examples are typical for one particular hearing aid system used by the inventors. It should be understood by those skilled in the art that the numerical values of the detection parameters are strongly influenced by the hearing aid system itself and the nature of the feedback paths encountered in a real-life hearing aid use situation and some can vary by a factor of, for example, 2 or 3 from the exemplary values of the detection parameters provided herein.
  • the input sound level parameter is the sound level of the bandpass input signal 32-1 .
  • the sound level distance l d of the input sound level from the feedback threshold level l 0 provides an indication of the possibility that feedback is occurring for the bandpass input signal 32-1 .
  • the sound level distance l d may be monitored to detect the onset of feedback within the bandpass input signal 32-1 .
  • the onset of feedback i.e. feedback buildup
  • the presence of feedback can be detected when the magnitude of the input sound level crosses over the feedback threshold level l 0 .
  • a typical threshold level l o can be 48 dB, and l d can be 3 dB.
  • the value for the sound level distance l d can be much larger depending on the particular hearing aid system and the sensitivity desired for the detection of feedback buildup.
  • the input sound level variation parameter dl represents the amount of variability in the sound level of the bandpass input signal 32-1 .
  • This parameter is related to the feedback path, the compression ratio, and the attack and release times used by the compression unit of a non-linear hearing aid.
  • the onset of feedback in the bandpass input signal 32-1 could be detected when the input sound level variation dl is within a pre-specified sound level variation threshold.
  • the presence of feedback can also be detected in a similar way.
  • the parameter is system dependent, but a typical level variation threshold may have a value of 3 dB for detecting established feedback and the range for the level variation threshold for detecting the onset of feedback can be somewhat larger, e.g. 5 dB.
  • the input sound level modulation parameter fm represents the modulation of the input sound level due to the feedback path and the compression characteristics of the non-linear hearing aid.
  • the presence of feedback in the bandpass input signal 32-1 can be detected when the input sound level modulation parameter fm has a value that is within a pre-specified modulation frequency range.
  • the value of the input sound level modulation parameter fm may be in the range of a few Hz to a few hundred Hz during feedback.
  • This parameter is also used to detect the onset of feedback.
  • the input sound level modulation parameter fm can be in the 3-5 Hz range for detecting the onset and presence of feedback. Again, this parameter is strongly influenced by the actual hearing aid system and other systems may require a much larger upper limit for this range.
  • the rise time duration parameter t r represents the amount of time required for the magnitude of the input sound level to cross over the feedback threshold level l 0 . If the rise time duration t r indicates an input sound level that persistently increases for an amount of time greater than a pre-specified rise time duration threshold, then the onset of feedback can be detected in the bandpass input signal 32-1 . Alternatively, the presence of feedback can be detected based on the time duration t d for which the input sound level is greater than the feedback level threshold l 0 . The time duration t d can be compared to a pre-specified time duration threshold. This parameter is system dependent. A typical range of values for t r and t d is 20 to 50 ms and 40 to 100 ms respectively. Preferably, the values of t r and t d can be set to 40 ms and 50 ms respectively. However, this parameter is also strongly system dependent.
  • the gain differential parameter represents the difference in the calculated gain that is applied to the bandpass input signal 32-1 compared to the maximum gain that can be applied.
  • the maximum gain for the hearing aid system may vary depending on frequency and is determined when the hearing aid system is fitted to the user.
  • the presence of feedback can be detected in the bandpass input signal 32-1 when the calculated gain is close to the maximum gain, i.e. the gain differential is small and less than a pre-specified gain differential margin as will be described further below.
  • Some exemplary gain differential margins may be 5, 10, 15 or 20 dB.
  • the rate at which the gain differential decreases in magnitude can be used to indicate the onset of feedback, or the presence of feedback.
  • the feedback detector 42-1 may combine two or more of the above-noted parameters when determining whether a feedback condition is present within the input band signal 32-1 (i.e. feedback is present or the onset of feedback is eminent).
  • the inventors have found that combining two or more of the parameters results in more reliable detection of potential feedback. While using fewer parameters to detect the onset or the presence of a feedback condition can lead to a successful result, the inventors have found that using all possible parameters together results in a more reliable and a rapid suppression or prevention of feedback.
  • monitoring a bandpass input signal during the time period t r leads to detection during the buildup phase, and a gain reduction, to address the buildup of feedback as described below, can already begin to be applied during the time period t d .
  • the inventors have observed cancellation of feedback in a time as short as 50 ms after onset. When feedback is already present, feedback detection and suppression can typically occur within 60 ms.
  • the gain differential parameter is particularly important to the detection of feedback during the initial feedback buildup stage.
  • the feedback signal is quickly distinguishable from normal speech or background noise, because the gain of the hearing aid system 10 usually reaches a maximum value during the feedback buildup phase.
  • the actual gain is effectively reduced by the compression in the system. Since the feedback pattern can be quickly recognized in a short time, during the feedback buildup phase or during the occurrence of feedback, each detection parameter contributes to the certainty of feedback detection.
  • Figure 4 is directed towards the case of a non-linear hearing aid that uses a compression algorithm
  • some of the above-noted parameters can be used for detecting a feedback condition for a bandpass input signal in a linear hearing aid.
  • These parameters include input sound level variation, rise time duration and input sound level.
  • the linear hearing aid is a special case of the more general non-linear hearing aid system, and the typical values for the detection parameters stated above also apply to the linear hearing aid case.
  • the corresponding adaptive feedback canceller 44-1, 44-2, ..., 44-N applies a gain modification factor G-1, G-2, ..., G-N for adjusting the gain applied to the bandpass input signal having the feedback condition.
  • the magnitude of the gain modification factor and the amount of time for which the gain modification factor is applied are controlled so that the hearing aid system delivers the output sound signal 40 to the user of the hearing aid system 10 with natural sound quality, required signal strength, and without feedback.
  • the gain curve 50 provides the calculated gain value based on the input sound level. For example, for input sound level l e , the calculated gain value is G e .
  • the gain curve 50 is piecewise linear with two knee-points K 1 and K 2 .
  • the gain curve 50 provides small gain values for low input sound levels (i.e. close to the origin of the gain curve 50) since these input sound levels are associated with microphone noise, environmental noise and system noise.
  • the gain curve 50 then increases linearly to the first knee-point K 1 at which point the gain curve 50 has a maximum gain value. After the first knee-point K 1 , compression begins to be applied.
  • the magnitude of the calculated gain value corresponding to the input sound levels above the first knee-point K 1 begins to decrease.
  • the location of the first knee-point K 1 depends on the hearing loss of the user of the hearing aid system 10 but may typically be 45 dB SPL, for example.
  • the magnitude of the calculated gain value begins to decrease at a faster rate, since sounds associated with input sound levels above K 2 correspond to a very loud sound such as airplane noise.
  • the hearing aid system 10 may contain a different gain curve for each of the N frequency bands.
  • each gain curve may have a similar general shape but different values for the knee-points, or both the shapes and knee-points may differ from band to band.
  • a gain curve for a linear hearing aid system is a special case of the gain curve for a non-linear hearing aid system.
  • the gain curve for the linear hearing aid system usually exhibits a constant gain value up to the knee-point after which the gain curve decreases.
  • the gain curves shown herein are exemplary and it is well known to those skilled in the art, that the slopes of these curves could be linear or curved and that the knee points can be abrupt or rounded.
  • the adaptive feedback canceller 44-1 defines a feedback margin with respect to the maximum gain value of gain curve 50.
  • the lower level of the feedback margin defines a maximum allowable gain value for the bandpass input signal 32-1 , which results because of the presence of a feedback condition.
  • the feedback margin is a fixed feedback margin, however, the adaptive feedback canceller 44-1 may also apply an adaptive feedback margin as discussed below.
  • Exemplary values for the magnitude of the fixed feedback margin are 6, 10, 12 or 18 dB. Through experiments the inventors have found that a fixed feedback margin of 12 dB is preferable for adaptively canceling feedback while minimally disrupting the sound quality of the output sound signal 40 .
  • the adaptive feedback canceller 44-1 calculates a gain modification factor G-1 such that the actual gain value that is applied to the bandpass input signal 32-1 is less than or equal to the maximum allowable gain value when a feedback condition is detected within the bandpass input signal 32-1 .
  • the adaptive feedback canceller 44-1 preferably calculates the magnitude of the gain modification factor such that the actual gain value is limited to the maximum allowable gain value.
  • the adaptive feedback canceller 44-1 calculates gain modification factors for a narrow range of input sound level values (i.e. from input sound level l 1 to input sound level l 2 in the example of Figure 6). This provides minimal disruption to the sound quality of the overall dynamic sound signal that is experienced by the user of the hearing aid system 10 .
  • the adaptive feedback canceller 44-1 preferably adaptively calculates the gain modification factor based on the amount that the calculated gain value is over the maximum allowable gain value. For example, assuming a maximum allowable gain value of 40 dB, the adaptive gain factor for a first calculated gain value of 43 dB is preferably -3 dB and the adaptive gain factor for a second calculated gain value of 48 dB is preferably -8 dB. The maximum gain reduction provided by the gain modification factor occurs when the input sound level coincides with the first knee-point K 1 . Accordingly, the adaptive feedback canceller 44-1 is not overly aggressive when calculating the gain modification factor for all input sound levels for which a feedback condition exists.
  • the gain adjustment provided by the gain modification factor is temporal and will be adaptively applied and adaptively removed in accordance with the continuous feedback detection provided by the feedback detector 42-1 . This will allow the overall output sound signal, which may contain speech and/or music, to be essentially unaffected since the actual gain has been temporarily modified in time and frequency in order to remove feedback in one or more of the bandpass input signals 32-1, 32-2, .... 32-N for which a feedback condition has been detected.
  • the adaptive feedback canceller 44-1 works well in most situations when the fixed feedback margin is applied. However, because a fixed feedback margin is used, the adaptive gain modification factor may not necessarily be optimized to provide the best performance for a wide variety of different types of hearing aid systems and for different degrees of feedback. For instance, if a large fixed feedback margin is used, the adaptive feedback canceller 44-1 might over-react to feedback and reduce the gain more than is required. This may cause unnecessary and undesirable sound quality degradation in the output sound signal 40. In the other extreme, if a small fixed feedback margin is applied, the adaptive feedback canceller 44-1 might under-react to the feedback and not cancel the feedback completely.
  • the adaptive feedback canceller 44-1 adaptively adjusts the magnitude of the feedback margin in order to optimize feedback cancellation and the sound quality of the output sound signal 40 .
  • the adaptive feedback canceller 44-1 applies a feedback margin having a first magnitude that is a low value such as 3 dB, for example. If the feedback is cancelled immediately, as indicated by the feedback detection signal FD-1 provided by the feedback detector 42-1, the adaptive feedback canceller 44-1 will continue to apply the low magnitude feedback margin. However, if feedback still exists or continues to buildup, the adaptive feedback canceller 44-1 adaptively increases the magnitude of the adaptive feedback margin. In this fashion, the magnitude of the adaptive feedback margin is progressively increased until the feedback is cancelled or the feedback buildup is stopped.
  • the step-size that is used in increasing the adaptive feedback margin may comprise large steps for aggressively attacking the feedback condition.
  • the step-size may comprise small steps to optimize the balance between canceling the feedback condition and maintaining good sound quality in the output sound signal 40 at all times.
  • the speed with which, or the time duration that expires before, the magnitude of the adaptive feedback margin is increased can be varied to aggressively attack the feedback condition.
  • the adaptive feedback canceller 44-1 may wait 5 ms before increasing the magnitude of the adaptive feedback margin.
  • the time duration can also depend on the reaction time (i.e. attack and release times) of the hearing aid system. The time duration should be short (i.e. fast) for a hearing aid system with fast attack and release times.
  • the adaptive feedback canceller 44 defines an adaptive feedback margin having three possible magnitudes A 1 , A 2 and A 3 with respect to the maximum gain value of gain curve 50. Accordingly, the three magnitudes A 1 , A 2 and A 3 of the adaptive feedback margins result in three maximum allowable gain values MAG 1 , MAG 2 and MAG 3 and three corresponding actual gain curves 56, 58 and 60.
  • the adaptive gain modification factors are calculated for a different input sound level range and the range of the values of the adaptive gain modification factors (which relates to the magnitudes of the adaptive feedback margins A 1 , A 2 and A 3 ) also increases.
  • the adaptive feedback margin having magnitude A 1 the input sound levels in the range of l 3 to l 4 are modified by the adaptive gain modification factor.
  • the adaptive feedback margin having magnitude A 2 the input sound levels in the range of l 5 to l 6 are modified by the adaptive gain modification factor.
  • an adaptive feedback margin having magnitude A 3 the input sound levels in the range of l 7 to l 8 are modified by the adaptive gain modification factor. Accordingly, an adaptive feedback margin with the largest magnitude A 3 affects the largest range of input sound levels by possibly the largest amount.
  • the hearing aid system 10 may employ a variety of combinations for the feedback margins.
  • the hearing aid system 10 may employ only fixed feedback margins or only adaptive feedback margins.
  • the hearing aid system 10 may employ a combination of both fixed and adaptive feedback margins at the same time.
  • the sub-units of the adaptive feedback cancellation unit 18 that process bandpass input signals which correspond to a low frequency portion of the input frequency spectrum may employ fixed feedback margins while the sub-units of the adaptive feedback cancellation unit 18 that process bandpass input signals which correspond to a high frequency portion of the input frequency spectrum, which are susceptible to feedback path variations, may employ adaptive feedback margins.
  • the volume control allows the user to adjust the sound level of the time domain output signal 36 (which affects the output sound signal 40 in a likewise fashion) by turning a potentiometer wheel or depressing a push button switch.
  • the amount of adjustment provided by the volume control may range, for example, from 0 to 10 dB or 0 to 30 dB with step-size adjustments that can be as fine as 0.1 dB. Accordingly, the user has the ability to adjust the actual gain of the hearing aid system through volume control which effects the function of the adaptive feedback cancellers 44-1 . Accordingly, the volume control must be taken into account by the adaptive feedback canceller 44-1.
  • the volume control may be positioned before or after the feedback cancellation unit 18. In practice, the volume control may be applied prior to the analysis unit 16 or after the synthesis unit 20. Alternatively, the volume control may be placed between the analysis unit 16 and the adaptive feedback cancellation unit 18 or between the adaptive feedback cancellation unit 18 and the synthesis unit 20 .
  • FIG. 8 shown therein is an alternative embodiment of the hearing aid system 100 that incorporates a volume control unit 148 .
  • the majority of the components of the hearing aid system 100 function in the same way as for hearing aid system 10 and have been numbered in a likewise fashion but offset by a factor of 100 .
  • the volume control unit 148 of the hearing aid system 100 is located upstream from the analysis unit 116 .
  • the first actual gain curve 52 corresponds to the situation in which the volume control unit 148 is at a maximum setting, i.e., the user of the hearing aid system 100 has not used the volume control unit 148 to decrease the sound level of the output sound signal 140 .
  • the adaptive feedback canceller 144-1 calculates the adaptive gain modification factor for input sound levels in the range of l1 to l2 which corresponds to line segment AB on the actual gain curve 52.
  • the second actual gain curve 152 corresponds to the situation in which the user of the hearing aid system 100 has used the volume control unit 148 to decrease the sound level of the output signal 140 by an amount VC dB. In this case, the actual gain curve 152 is shifted downwards by the amount VC dB. The magnitude of the fixed feedback margin and the maximum allowable gain value are not affected by the reduction in actual gain produced by the volume control unit 148 .
  • the adaptive feedback canceller 144-1 calculates the adaptive gain modification factor for input sound levels in the range of l 1 ' to l 2 ' which corresponds to line segment CD on the actual gain curve 152.
  • the input sound level range of l 1 ' to l 2 ' is smaller than the input sound level range of l 1 to l 2 . This is also seen by the smaller size of dotted portion 154 compared to the dotted portion 54 which indicates that the range of values for the magnitude of the adaptive gain modification factor is smaller with a reduced volume control setting.
  • the first actual gain curve 52 corresponds to the situation in which the volume control unit 148 is at a maximum setting and the adaptive feedback margin has a magnitude of A 3 with a corresponding maximum allowable gain value of MAG 3 .
  • the adaptive feedback canceller 144-1 calculates the adaptive gain modification factor for input sound levels in the range of l 7 to l 8 which corresponds to line segment AB on the actual gain curve 52.
  • the second actual gain curve 160 corresponds to the situation in which the user of the hearing aid system 100 has used the volume control unit 148 to decrease the sound level of the output signal 140 by an amount VC dB thereby shifting the curve 160 downwards by the amount VC dB.
  • the magnitude of the adaptive feedback margin A 3 and the maximum allowable gain value MAG 3 are not affected by the reduction in actual gain produced by the volume control unit 148 .
  • the adaptive feedback canceller 144 calculates the adaptive gain modification factor for input sound levels in the range of l 7 ' to l 8 ' which corresponds to line segment CD on the actual gain curve 160.
  • the input sound level range of l 7 ' to l 8 ' is smaller than the input sound level range of l 7 to l 8 . This is also seen by the smaller size of dotted portion 164 compared to the dotted portion 54 which indicates that the range of possible values for the magnitude of the adaptive gain modification factor is smaller with a reduced volume control setting.
  • FIG. 11 shown therein is another alternative embodiment of the hearing aid system 200 that incorporates a volume control unit 248.
  • the majority of the components of the hearing aid system 200 function in the same way as for hearing aid system 10 and have been numbered in a likewise fashion but offset by a factor of 200.
  • the volume control unit 248 of the hearing aid system 200 is located downstream from the synthesis unit 216 .
  • the adaptive feedback canceller 244 applies a fixed feedback margin (NVC) with an associated maximum allowable gain value MAG NVC (NVC means that the volume control setting is at a maximum and that there has not been a reduction in the volume control setting).
  • NVC fixed feedback margin
  • MAG NVC maximum allowable gain value
  • the second actual gain curve 252 corresponds to the situation in which the user of the hearing aid system 200 has used the volume control unit 248 to decrease the sound level of the output signal 240 by an amount VC dB.
  • the actual gain curve 252 is shifted downwards by the amount VC dB with respect to actual gain curve 52 .
  • the magnitude of the fixed feedback margin and the maximum allowable gain value are affected by the adjustment in actual gain produced by the volume control unit 248 and are shifted downwards by the same amount of VC dB.
  • the adaptive feedback canceller 244-1 is effectively applying a fixed feedback margin (WVC) with an associated maximum allowable gain value MAG wvc with respect to the maximum gain of the hearing aid system 200 (WVC means that the volume control setting is at a reduced setting).
  • WVC fixed feedback margin
  • the adaptive feedback canceller 244 calculates the adaptive gain modification factor for input sound levels in the same range of l 1 to l 2 corresponding to line segment CD, which has the same length as line segment AB, on the actual gain curve 252. Further, dotted portion 254 is the same as the dotted portion 54 which indicates that the range of values for the magnitude of the adaptive gain modification factor remains the same with a reduced volume control setting in this case.
  • the first actual gain curve 52 corresponds to the situation in which the volume control unit 248 is at a maximum setting and the adaptive feedback margin has a magnitude of A 3NVC with a corresponding maximum allowable gain value of MAG 3NVC .
  • the adaptive feedback canceller 244-1 calculates the adaptive gain modification factor for input sound levels in the range of l 7 to l 8 which corresponds to line segment AB on the actual gain curve 52 .
  • the second actual gain curve 260 corresponds to the situation in which the user of the hearing aid system 200 has used the volume control unit 248 to decrease the sound level of the output signal 240 by an amount VC dB thereby shifting the curve 260 downwards by the amount VC dB with respect to actual gain curve 52.
  • the adaptive feedback canceller 244-1 calculates the adaptive gain modification factor for input sound levels in the range of l 7 to l 8 corresponding to line segment CD , which has the same length as line segment AB , on the actual gain curve 260 .
  • the dotted portion 264 has the same size compared to the dotted portion 54 which indicates that the range of values for the magnitude of the adaptive gain modification factor remains the same with a reduced volume control setting in this case.
  • the inventors have found that, with the hearing aid system of the present invention, detection and cancellation of the feedback condition takes place in less than 100 ms which is before feedback is fully built up and becomes noticeable to the hearing aid user. In contrast, most prior art feedback cancellation technologies usually require in excess of 400 ms for feedback detection and cancellation during which the feedback has already built up to a steady state level which can be extremely uncomfortable to the hearing aid user.
  • the inventors have also found that the inventive hearing aid system is capable of detecting and canceling multiple feedback paths occurring in several of the N frequency regions. For example, the inventors have observed as many as seven feedback frequencies at one time.
  • adaptive feedback cancellation scheme of the present invention may be employed for any type of audio system and need not be restricted to hearing aid systems.
  • the application of this adaptive feedback cancellation scheme may involve having alternative shapes for the gain curves but the underlying principles of the invention would still apply.
  • the units of the hearing aid system are typically implemented in a digital signal processor. Accordingly, the functionality of the feedback detector, the adaptive feedback canceller and the multiplier of one of the sub-units of the adaptive feedback cancellation unit may be implemented within the same means.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
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  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)
  • Circuit For Audible Band Transducer (AREA)
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US7092532B2 (en) 2006-08-15
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CA2462322A1 (en) 2004-09-30
CN1612640A (zh) 2005-05-04

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